Point of care urine analyzer

ABSTRACT

There is provided a urine analysis device for bed side monitoring of a patient, comprising: an inlet sized and shaped for fluid communication with a urine collecting tube that receives urine from a patient; a drip chamber through which the urine flows towards an outlet; at least one sensor that analyzes each drop of urine and estimates a respective volume of each drop; a timing element that measures a reference time for each drop; a program store storing code; and at least one processing unit coupled to the program store for implementing the stored code, the code comprising: code to calculate a urine output flow rate of the urine output flowing through the chamber according to the estimated volume of each drop of the urine and the reference time for each drop; and code to output the urine output flow rate.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/228,115 filed on Aug. 4, 2016, which claims the benefit of priorityunder 35 USC § 119(e) of U.S. Provisional Patent Application No.62/201,118 filed Aug. 5, 2015, the contents of which are incorporatedherein by reference in their entirety.

FIELD AND BACKGROUND OF THE INVENTION

The present invention, in some embodiments thereof, relates to urineanalysis and, more specifically, but not exclusively, to systems andmethods for point of care urine analysis.

Urine flow and/or measurement of urine constituents are used by themedical community as an indicator of health in general, and inparticular in the case of hospitalized patients and/or post surgicalpatients. Current medical practice is based on measuring urine output ofpatients (e.g., using an indwelling catheter) by manual observationusing grades marked on a urine collection bag. Decreased urine flow maybe indicative of, for example, acute kidney injury (AKI). Increasedurine flow may be indicative of, for example, post obstructive dieresis(POD). Urine analysis is performed by using a urine test strip that ismanually dipped into the urine. Colors appearing on the test strip arevisually compared to a reference. When more accurate values arerequired, a urine sample is sent to a lab for analysis.

SUMMARY OF THE INVENTION

According to an aspect of some embodiments of the present inventionthere is provided a urine analysis device for bed side monitoring of apatient, comprising: an inlet sized and shaped for fluid communicationwith a urine collecting tube that receives urine from a patient; a dripchamber through which the urine flows towards an outlet; at least onesensor that analyzes each drop of urine and estimates a respectivevolume of each drop; a timing element that measures a reference time foreach drop; a program store storing code; and at least one processingunit coupled to the program store for implementing the stored code, thecode comprising: code to calculate a urine output flow rate of the urineoutput flowing through the chamber according to the estimated volume ofeach drop of the urine and the reference time for each drop; and code tooutput the urine output flow rate.

Optionally, the urine analysis device further comprises code to identifya trend in the urine output flow rate indicative of a decrease orincrease in the urine output flow rate and to present an indication ofthe trend on a graphical user interface (GUI) presented on a display.

Optionally, the urine analysis device further comprises code to identifya trend in the urine output flow rate indicative of acute kidney injury(AKI) and to present an indication of the detected AKI on the GUI.

Optionally, the urine analysis device further comprises code to generatean alert when an analysis of the trend is predictive of a future urineflow rate value falling outside of a predefine tolerance range.

Optionally, the trend is identified according to a least squareregression analysis conducted using a sliding window of a predefinednumber of urine output flow rate measurements.

Optionally, the code includes instructions to calculate an instantaneousurine output flow rate, and present the instantaneous urine output flowrate on the GUI.

Optionally, the urine analysis device further comprises an interface toa display, and code that instructions a presentation of a graphical userinterface (GUI) on the display that includes the measured urine outputflow rate and an identified trend in the urine output flow rate.

Optionally, the sensors analyzes urine flowing within the drip chamber,prior to the flowing urine entering a urine collection bag in fluidcommunication with the outlet.

Optionally, the sensor comprises a fast gated camera that is activatedby a photo detector disposed above the camera to capture at least oneimage of each drop, and further comprising code to estimate the volumeof each drop according to an analysis of the at least one image of thedrop. Optionally, the fast gated camera includes a high resolution imagesensor selected from a group consisting of: a complementary metal oxidesemiconductor (CMOS) module, and a charge couple device (CCD) module.

Optionally, the code comprising code instructions to calculate a type ofcontent of the drop by combining a plurality of time sequentiallyordered calculated values of widths of the drop and a plurality of timesequentially ordered values of widths of a plurality of exemplary drops,the plurality of exemplary drops comprising of different content typesof liquid, wherein a respective drop is calculated to be of a one of aplurality of the types of liquid.

Optionally, the drip chamber is transparent, and wherein the sensorcomprises an optical sensor for estimating the volume of the urine dropthrough the walls of the transparent drip chamber.

Optionally, the urine analysis device further comprises a drip formationelement that forms the urine outputted by the patient into the drops ofurine that one drop at a time inside the drip chamber.

According to an aspect of some embodiments of the present inventionthere is provided a urine analysis device for bed side monitoring of apatient, comprising: an inlet sized and shaped for fluid communicationwith a urine collecting tube that receives urine from a patient; a dripchamber through which the urine flows towards an outlet; a plurality ofconstituent measuring elements positioned within the drip chamber belowthe inlet to contact drops of urine received from the patient, theconstituent measuring elements arranged on a rotating element that turnsa predefined amount at a predefined time interval to expose another ofthe constituent measuring elements to a new drop of urine, wherein eachof the constituent measuring elements estimates a concentration of adifferent urine constituent in respective drops of urine; and at leastone sensor coupled to the constituent measuring elements to output aconstituent signal indicative of a measurement of the respective urineconstituent by the respective measuring element.

Optionally, the urine analysis device further comprises a program storestoring code; and at least one processing unit coupled to the programstore for implementing the stored code, the code comprising: code toanalyze the constituent signal for each respective urine constituent tocalculate at least one of a concentration and the presence of therespective urine constituent; and code to output the at least one ofconcentration and presence of each respective urine constituent.

Optionally, the constituent measuring elements and the at least onesensor comprise respective lab-on-chips each designed to estimate atleast one of a concentration and a presence of a respective urineconstituent.

Optionally, each of the constituent measuring elements includes animpregnated strip media that changes to a different color according tothe concentration of the respective constituent, and wherein the atleast one sensor comprises a color camera arranged to sense the changedcolor of each respective constituent measuring element on the rotatingelement at each turn and output and outputs a signal indicative of thesensed changed color, and code instructions that analyze the signal tocalculate the concentration of the respective constituent correspondingto the sensed changed color.

Optionally, the constituent signal is generated based on an analysisconducted in urine flowing within the drip chamber, prior to the flowingurine entering a urine collection bag in fluid communication with theoutlet.

Optionally, the urine analysis device further comprises a sensor thatdetect the drops and outputs a signal to trigger the rotation of therotating element.

According to an aspect of some embodiments of the present inventionthere is provided a urine analysis device for bed side monitoring of apatient, comprising: an inlet sized and shaped for fluid communicationwith a urine collecting tube that receives urine from a patient; a dripchamber through which the urine flows towards an outlet; a light sourcethat creates a light directed to pass through at least one drop of theurine of the patient; a dispersion element receives the light thatpassed through the at least drop of the urine and outputs a lightspectrum; a multi element detector that receives the light spectrum on aplurality of light detector elements and output a signal indicative ofthe intensity of the received light spectrum as a function of thewavelength of light according to the respective light detector elements;a program store storing code; and at least one processing unit coupledto the program store for implementing the stored code, the codecomprising: code to analyze the signal and calculate a value of at leastone urine constituent; and code to output the value of the at least oneurine constituent.

Optionally, the light source is a tunable light source capable ofemitting a range of wavelengths.

Optionally, the light source is a sweeping source, wherein the spectraldispersion element splits the light source to a first portion that isreflected at least by the urine and directed to a sub-set of elements ofthe multi element detector and a second portion that passes through theurine and directed to another detector having a single detector, whereinthe light source is swept as a function of time, and code instructionsto calculate an osmolarity of the urine according to an analysis of thesignals outputted by the multi element detector and the anotherdetector.

Optionally, the urine analysis device further comprises aninterferometer that includes a tunable source of the light sourcecapable of emitting a range of wavelengths, a beam splitter that splitsthe light emitted by the light source to a reference path and a paththrough the urine, and a mechanism to combine the reference path lightand the light of the path through the urine into a combined spectralsignal, and further comprising code instructions to analyze the combinedspectral signal to calculate concentration of at least one urineconstituent.

Optionally, the urine analysis device further comprises a transparentchamber positioned within the drip chamber and arranged to be constantlymaintained in a urine filled state, wherein the light of the paththrough the urine is directed through the transparent chamber.

Unless otherwise defined, all technical and/or scientific terms usedherein have the same meaning as commonly understood by one of ordinaryskill in the art to which the invention pertains. Although methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of embodiments of the invention, exemplarymethods and/or materials are described below. In case of conflict, thepatent specification, including definitions, will control. In addition,the materials, methods, and examples are illustrative only and are notintended to be necessarily limiting.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

Some embodiments of the invention are herein described, by way ofexample only, with reference to the accompanying drawings. With specificreference now to the drawings in detail, it is stressed that theparticulars shown are by way of example and for purposes of illustrativediscussion of embodiments of the invention. In this regard, thedescription taken with the drawings makes apparent to those skilled inthe art how embodiments of the invention may be practiced.

In the drawings:

FIG. 1 is a block diagram of components of a system that uses formedurine drops to estimate a flow rate of urine outputted by a patient(using the volume measured for each drop), and/or estimatesconcentration of one or more constituents in the outputted urine, inaccordance with some embodiments of the present invention;

FIG. 2 is a flowchart of a method of operation of the system of FIG. 1,in accordance with some embodiments of the present invention;

FIG. 3 is a schematic of an environment in which the system of FIG. 1 isimplemented, in accordance with some embodiments of the presentinvention;

FIG. 4 is a schematic of an exemplary urine analyzer that outputssignals used to estimate the volume of a drop of urine and/or estimatethe urine output flow rate, in accordance with some embodiments of thepresent invention;

FIG. 5 is a schematic of an exemplary urine analyzer that analyzesvolume of urine drops and outputs signals for calculation of the urineoutput flow rate, in accordance with some embodiments of the presentinvention;

FIG. 6A is a schematic of an exemplary drip chamber and/or inspectioncapsule, in accordance with some embodiments of the present invention;

FIG. 6B is a schematic of the drip chamber and/or inspection chamber ofFIG. 6A positioned to accommodate measurements performed by flow sensorand/or timing mechanism on the falling drops, in accordance with someembodiments of the present invention;

FIG. 7 is a schematic of processed drop images obtained by a sensor, inaccordance with some embodiments of the present invention;

FIG. 8 is a schematic of the exemplary urine analyzer device describedwith reference to FIG. 5, including a constituent measurement devicethat measures the constituents in the urine, in accordance with someembodiments of the present invention;

FIG. 9 is a schematic of an implementation of a rotating apparatus thatrotates to contact each constituent measuring element with a differentdrop of urine, in accordance with some embodiments of the presentinvention;

FIG. 10 is a schematic depicting components of a spectral analysissystem for measuring the constituent(s) of urine, and a sample spectraloutput, in accordance with some embodiments of the present invention;

FIG. 11 is a schematic of an exemplary implementation of a constituentanalyzer based on spectral analysis, in accordance with some embodimentsof the present invention;

FIG. 12 is a schematic of another exemplary implementation of theconstituent analyzers based on spectral analysis, in accordance withsome embodiments of the present invention;

FIG. 13 includes signals and/or graphs used to extract concentrations ofone or more urinary constituents from the signal(s) outputted by urineanalyzers, in accordance with some embodiments of the present invention;

FIG. 14 is an example of a calibration curve for estimatingconcentration of a certain urinary constituent, in accordance with someembodiments of the present invention;

FIG. 15 is a schematic of an exemplary GUI presented on a displayindicating the measured urine output flow rates, in accordance with someembodiments of the present invention; and

FIG. 16 is a flowchart of a method for calculating concentration of oneor more urinary constituents for generating the alert, in accordancewith some embodiments of the present invention.

DESCRIPTION OF SPECIFIC EMBODIMENTS OF THE INVENTION

The present invention, in some embodiments thereof, relates to urineanalysis and, more specifically, but not exclusively, to systems andmethods for point of care urine analysis.

An aspect of some embodiments of the present invention relates to aurine analysis device (and/or a method for operation of the urineanalysis device implemented by code instructions executed by one or moreprocessors) that calculates a urine outflow rate of urine outputted by apatient according to an estimated volume of one or more drops of urineand a time stamp indicative of formation of each respective drop beinganalyzed. The urine outputted by the patient (e.g., received from anindwelling urinary catheter) is formed into single dropped by a dripperelement, for example, a hollow tube. A sensor analyzes one or more dropsof urine and estimates the volume of each respective drop. A timingelement determines the time for each respective drop, optionally as atime stamp. Code instructions executable by one or more processorscalculate the urine outflow rate according to the volume and time stampof the drops.

The urine analysis device provides bedside monitoring of the real-timeurine output of the patient, for example, in comparison to standardmanual methods in which urine accumulates for hours in a collection bag,and the accumulated volume is read visually using markings on the bag.Such methods require collection of urine for many hours before it can bedetermined whether the urine output is normal or abnormal, and thereforesuch methods are prone to error due to inaccuracies in volume and/ortime estimations. The real-time data provided by the urine analysisdevice may be used by health care providers to provide treatment to thepatient sooner using accurate values and/or based on predicted values,and/or prevent the patient from deteriorating and/or disease progressionwith earlier treatment provided by the real-time data and/or predicteddata.

Optionally, a trend is identified (e.g., by code instructions executableby one or more processors) in the urine output flow rate. The identifiedtrend is predictive of an increase or a decrease in the value of theurine output flow rate relative to a predefined tolerance range thatrepresents a safe range of urine output flow rates for the patient.

Optionally the trend is indicative of acute kidney injury (AKI). Thetrend may be represented on a graphical user interface (GUI) thatpresents the calculated urine flow rate values, for example, as an arrowbased on a regression line of the urine flow rate data points. An alertis optionally generated (e.g., flashing warning message on the GUI) whenthe trend is indicative that the urine output flow rate is predicted toreach a value outside of the predefined tolerance range in the nearfuture (e.g., in the next hour, 6 hours, or 12 hours, or other futuretimes).

Optionally, an instantaneous urine output flow rate is estimated (e.g.,by code instructions executable by one or more processors) based on atleast two urine drops. The instantaneous urine output flow rate may bepresented on the GUI, and/or plotted as a point on a graph of urine flowrate as a function of time, which may be used to identify the trend.

The instantaneous urine output flow rate may be a more accurate and/orreal-time representation of the state of the patient, for example, incomparison to standard manual methods in which the average urine flowrate is estimated using accumulated urine over many hours. Alternativelyor additionally, the urine output flow rate is measured over a timeinterval that may be shorter than a time interval used by manualmethods, for example, a half hour, or an hour. The urine output flowrate is measured using a sample or most or all of the urine drops thatare outputted by the patient during the time interval. The urine outputflow rate may provide a more accurate representation of the state of thepatient, rather than having to wait for several hours for sufficienturine to accumulate for a manual reading.

The urine analysis device (and/or code instructions executed by one ormore processors that perform the urine analysis) described hereinprovides automatic monitoring (e.g., continuous, periodic, and/or eventbased) of patients that is used to detect early changes in the patient'sstate of health, for example, early onset of AKI, urinary retention,urinary tract infection, and early onset of POD. The predictive trendmay predict early progression to abnormal health states, for example,progression to AKI.

An aspect of some embodiments of the present invention relates to aurine analysis device (and/or a method for operation of the urineanalysis device implemented by code instructions executed by one or moreprocessors) that measures real-time values of one or more urinaryconstituents in urine outputted by the patient. Exemplary valuesinclude: the concentration measured for each individual constituent, thepresence of each individual constituent using a threshold (e.g., zero,or other value), urine osmolarity, and urine osmolality.

The urine analysis device performs measurements of a different urineconstituent for each sequentially received drop(s) of urine. Optionally,each sequential single drop or group of drops is used for measuring adifferent single constituent in the drop. For example, in contrast tostandard manual methods, in which a urine dipstick is inserted into alarge volume of urine for measurement of multiple constituents using thesame urine volume. Alternatively or additionally, the single drop may beused to measure osmolality and/or osmolarity.

Optionally, each sequentially formed drop(s) falls onto a measuringelement designed to measure a different constituent. Exemplary measuringelements include multiple lab-on-chip (LOC) units each designed tomeasure a different constituent, and media each designed to change to adifferent color according to a concentration of the respectiveconstituent being measured by the respective media. A color camera maysense the color of each media and generate a signal indicative of thecolor. The signal may be analyzed using instruction code to estimate theconcentration of the constituents. Alternatively or additionally, theLOC and/or other measuring elements may be used to measure osmolarityand/or osmolality.

Optionally, the measuring elements are arranged along a surface of arotating element. The rotating element is controlled (e.g., by a motor)to turn a predefined amount to expose one or more sequentially formeddrops to the measuring elements (each measuring element may receive oneor more drops, for example, the minimum volume required to obtain anaccurate reading).

For example, the rotating element turns at a predefined rate of rotationor indexing (e.g., manually set by the operator, according tomanufacturer defined settings, based on formation of the drops and/ortrigged by each falling drop), such that each drop (or multiplesequential drops) falls on a different measuring element that measures adifferent constituent of the drop. Alternatively, the rotation istriggered by a sensor detecting the falling drop to rotate the rotatingelement to expose the next measuring element to the falling drop.

An aspect of some embodiments of the present invention relates tosystems and/or methods (e.g., code instructions executed byprocessor(s)) that estimates according to a spectral analysis, values ofone or more urinary constituents in urine outputted by the patient.Measurements of the urinary constituents may be performed at predefinedtime intervals, for example, every 15 minutes, or every 60 minutes, orother time interval.

Exemplary values include: the concentration measured for each individualconstituent, the presence of each individual constituent using athreshold (e.g., zero, or other value), urine osmolarity, and urineosmolality. A source of light (e.g., broadband light) is directedthrough the drop(s) of urine and optionally dispersed. Alternatively,the source of light is tunable, with narrow (e.g., single) bands ofwavelengths of light directed (e.g., sequentially) through the drop(s).The light that passed the drop(s) of urine is directed towards a singleor multi element detector array. Analysis code executed by one or moreprocessors may analyze the intensity generated by the elements of thearray, and/or according to which elements are activated, estimates theconcentration of one or more urinary constituents, for example, bycomparison with a standard reference (e.g., empirical measurementsand/or calculated using a mathematical model).

Optionally, a TIR prism (or other light splitting implementation) splitsthe light generated by the light source to a first portion that is atleast reflected by the urine and reaches a sub-set of the elements ofthe array. The light is split to a second portion that is transmittedthrough the urine and reaches a single element detector. The wavelengthof the light is varied over time. The signals of the detector array andthe single element detector are analyzed together to estimate theconcentration of one or more urine constituents and/or the osmolarityand/or osmolality of the urine.

Alternatively or additionally, the light from the light source is splitby a beam splitter into a reference beam, and a beam that passes throughone or more drops of urine. The reference beam is combined with thelight after passing through the urine, and analyzed to estimate theconcentration of one or more urine constituents and/or the osmolarityand/or osmolality of the urine. For example, the signals may besubtracted from one another to arrive at a signal indicative of theurinary constituents (i.e., removing the reference light from the lightthat passed through the urine).

The systems (including the urine analysis devices) and/or methodsdescribed herein (e.g., code instructions executed by one or moreprocessor(s)) address the technical problem of determining a urine flowand/or concentration of urinary constituent(s) that more accuratelyreflect the actual state of the patient. For example, current methodsrely on an average manual measurement obtained over many hours, forexample, manually reading a volume of urine collected in a bag over manyhours, and dividing by the estimated number of hours, and/or manuallydipping a urine stick into the volume of urine collected over manyhours. The proposed solution provides an on-site (i.e., at the patientbedside) estimation of the urine flow rate and/or concentration ofurinary constituents which more accurately relates to the real-timestate of the patient, rather than a retrospective average view that themanual methods provide. The estimation may be used to predict beforehandthat the patient urine flow rate and/or concentration of urinaryconstituents are trending towards leaving a safe predefined range.

The systems (including the urine analysis devices) and/or methodsdescribed herein (e.g., code instructions executed by one or moreprocessor(s)) improve an underlying technical process within thetechnical field of urinalysis. The systems and/or methods describedherein improve the process of estimating the patient urine flow rate(i.e., urinary output) and/or concentration of urine constituents, byproviding real-time measurements at the bedside using formed drops ofurine.

The systems (including the urine analysis devices) and/or methodsdescribed herein (e.g., code instructions executed by one or moreprocessor(s)) improve performance of a computing unit executing the codeinstructions that estimate the patient urinary flow rate and/or estimatethe concentration of urinary constituent(s). The improvement inperformance is obtained by reducing the processing time, processingresources, and/or memory resources to compute the patient urinary flowrate and/or estimate the concentration of urinary constituent(s). Theimprovement in performance is achieved at least in part by the analysisover a predefined time interval using small volumes of urine (based oncollecting one or several drops of urine), to calculate measurements,rather than, for example, collecting a large sample of urine over manyhours to perform the measurement(s).

The systems (including the urine analysis devices) and/or methodsdescribed herein (e.g., code instructions executed by one or moreprocessor(s)) are tied to physical real-life components, for example,using urine outputted by a patient (e.g., received from an indwellingurinary catheter), using electrical readings obtained from physicalsensor(s), and/or presenting the measurements on a physical display.

The systems (including the urine analysis devices) and/or methodsdescribed herein (e.g., code instructions executed by one or moreprocessor(s)) provide a unique, particular, and advanced technique ofreal-time or point-of-care (POC) estimation of the patient urine outputflow rate and/or concentration of constituents in the outputted urine.

Accordingly, the systems and/or methods described herein areinextricably tied to computer technology and physical hardware, toovercome an actual technical problem arising in calculating moreaccurate values for patient urinary output and/or urinary constituents.

Before explaining at least one embodiment of the invention in detail, itis to be understood that the invention is not necessarily limited in itsapplication to the details of construction and the arrangement of thecomponents and/or methods set forth in the following description and/orillustrated in the drawings and/or the Examples. The invention iscapable of other embodiments or of being practiced or carried out invarious ways.

The present invention may be a system, a method, and/or a computerprogram product. The computer program product may include a computerreadable storage medium (or media) having computer readable programinstructions thereon for causing a processor to carry out aspects of thepresent invention.

The computer readable storage medium can be a tangible device that canretain and store instructions for use by an instruction executiondevice. The computer readable storage medium may be, for example, but isnot limited to, an electronic storage device, a magnetic storage device,an optical storage device, an electromagnetic storage device, asemiconductor storage device, or any suitable combination of theforegoing.

A non-exhaustive list of more specific examples of the computer readablestorage medium includes the following: a portable computer diskette, ahard disk, a random access memory (RAM), a read-only memory (ROM), anerasable programmable read-only memory (EPROM or Flash memory), a staticrandom access memory (SRAM), a portable compact disc read-only memory(CD-ROM), a digital versatile disk (DVD), a memory stick, a floppy disk,and any suitable combination of the foregoing. A computer readablestorage medium, as used herein, is not to be construed as beingtransitory signals per se, such as radio waves or other freelypropagating electromagnetic waves, electromagnetic waves propagatingthrough a waveguide or other transmission media (e.g., light pulsespassing through a fiber-optic cable), or electrical signals transmittedthrough a wire.

Computer readable program instructions described herein can bedownloaded to respective computing/processing devices from a computerreadable storage medium or to an external computer or external storagedevice via a network, for example, the Internet, a local area network, awide area network and/or a wireless network. The network may comprisecopper transmission cables, optical transmission fibers, wirelesstransmission, routers, firewalls, switches, gateway computers and/oredge servers. A network adapter card or network interface in eachcomputing/processing device receives computer readable programinstructions from the network and forwards the computer readable programinstructions for storage in a computer readable storage medium withinthe respective computing/processing device.

Computer readable program instructions for carrying out operations ofthe present invention may be assembler instructions,instruction-set-architecture (ISA) instructions, machine instructions,machine dependent instructions, microcode, firmware instructions,state-setting data, or either source code or object code written in anycombination of one or more programming languages, including an objectoriented programming language such as Smalltalk, C++ or the like, andconventional procedural programming languages, such as the “C”programming language or similar programming languages.

The computer readable program instructions may execute entirely on theuser's computer, partly on the user's computer, as a stand-alonesoftware package, partly on the user's computer and partly on a remotecomputer or entirely on the remote computer or server. In the latterscenario, the remote computer may be connected to the user's computerthrough any type of network, including a local area network (LAN) or awide area network (WAN), or the connection may be made to an externalcomputer (for example, through the Internet using an Internet ServiceProvider). In some embodiments, electronic circuitry including, forexample, programmable logic circuitry, field-programmable gate arrays(FPGA), or programmable logic arrays (PLA) may execute the computerreadable program instructions by utilizing state information of thecomputer readable program instructions to personalize the electroniccircuitry, in order to perform aspects of the present invention.

Aspects of the present invention are described herein with reference toflowchart illustrations and/or block diagrams of methods, apparatus(systems), and computer program products according to embodiments of theinvention. It will be understood that each block of the flowchartillustrations and/or block diagrams, and combinations of blocks in theflowchart illustrations and/or block diagrams, can be implemented bycomputer readable program instructions.

These computer readable program instructions may be provided to aprocessor of a general purpose computer, special purpose computer, orother programmable data processing apparatus to produce a machine, suchthat the instructions, which execute via the processor of the computeror other programmable data processing apparatus, create means forimplementing the functions/acts specified in the flowchart and/or blockdiagram block or blocks. These computer readable program instructionsmay also be stored in a computer readable storage medium that can directa computer, a programmable data processing apparatus, and/or otherdevices to function in a particular manner, such that the computerreadable storage medium having instructions stored therein comprises anarticle of manufacture including instructions which implement aspects ofthe function/act specified in the flowchart and/or block diagram blockor blocks.

The computer readable program instructions may also be loaded onto acomputer, other programmable data processing apparatus, or other deviceto cause a series of operational steps to be performed on the computer,other programmable apparatus or other device to produce a computerimplemented process, such that the instructions which execute on thecomputer, other programmable apparatus, or other device implement thefunctions/acts specified in the flowchart and/or block diagram block orblocks.

The flowchart and block diagrams in the Figures illustrate thearchitecture, functionality, and operation of possible implementationsof systems, methods, and computer program products according to variousembodiments of the present invention. In this regard, each block in theflowchart or block diagrams may represent a module, segment, or portionof instructions, which comprises one or more executable instructions forimplementing the specified logical function(s).

In some alternative implementations, the functions noted in the blockmay occur out of the order noted in the figures. For example, two blocksshown in succession may, in fact, be executed substantiallyconcurrently, or the blocks may sometimes be executed in the reverseorder, depending upon the functionality involved. It will also be notedthat each block of the block diagrams and/or flowchart illustration, andcombinations of blocks in the block diagrams and/or flowchartillustration, can be implemented by special purpose hardware-basedsystems that perform the specified functions or acts or carry outcombinations of special purpose hardware and computer instructions.

As used herein, the terms estimate, measure, and calculate are sometimesinterchangeable, for example, when referring obtaining the urine outputflow rate and/or urine constituent concentrations. For example, thesensor(s) may perform measurements on the drops of urine. Themeasurements are used for calculating the urine output flow rate and/orthe urine constituent concentration. The calculated values represent anestimate of the actual values within the urine (i.e., based onextrapolation of the calculations performed on a sample of the urine).

Reference is now made to FIG. 1, which is a block diagram of componentsof a system 100 that uses formed urine drops to estimate a flow rate ofurine outputted by a patient (using the volume measured for each drop),and/or estimates concentration of one or more constituents in theoutputted urine, in accordance with some embodiments of the presentinvention. Reference is also made to FIG. 2, which is a flowchart of amethod of operation of system 100 of FIG. 1, in accordance with someembodiments of the present invention.

System 100 includes an inlet 102 for fluid communication with a urinecollecting tube that receives urine from the patient, for example, aconnection to an output of an indwelling catheter positioned within thebladder of the patient. The urine received from inlet 102 is formed intosingle sequentially falling drops by a drip formation element 104 (e.g.,hollow tube) that directs the drops into a drip chamber 106 having anoutlet 108 to a urine collection system (e.g., bag, waste drainage).Dripper element 104 may be implemented, for example, as an elongatedhollow tube that forms the drops at the end of the tube facing thegroup.

A flow sensor 110 (e.g., optical camera) analyzes each drop to estimatethe volume of the drop, which is used to estimate the urine output flowrate, as described herein. Flow sensor 110 may be implemented as anelectromagnetic sensor, optionally an optical sensor, optionally anoptical camera that captures one or more images of the drop, optionallyas the drop is falling through drip chamber 106.

Optionally, flow sensor 110 is a drop and/or drip measurement and/oranalyzer, for example, as described in International Patent ApplicationNo. WO2016084080, filed on Nov. 24, 2015, by the same inventors as thepresent application, incorporated herein by reference in its entirety.

A timing mechanism 112 (e.g., clock connected to the optical camera)measures a time reference for each drop. The time reference may be anabsolute time reference (e.g., the actual current time) and/or arelative time reference (e.g., the time elapsed from the previous drop,optionally resetting to zero for each new drop). The relative time isused to estimate the urine output flow rate, as described herein.Alternatively or additionally, timing mechanism 112 includes a counterthat counts the number of drops that fall within a predefined time, forexample, the number of drops per second, per minute, per hour, or otherperiods of time.

Constituent measuring element(s) 116 measure urinary constituents.Optionally, constituent measuring element 116 is implemented as a devicethat measures urine osmolarity and/or osmolality, for example, usingspectral analysis, and/or implemented as an interferometer, as describedherein. Alternatively or additionally, constituent measuring element(s)116 are implemented as multiple elements each designed to measure theconcentration (or presence of) a different urine constituent, forexample, lab-on-chip, color strips or other bio-chemical sensor (asdescribed herein).

Exemplary implementation of components 110, 112, and 116 are describedherein.

It is noted that system 100 may be implemented using differentcombinations of components to perform desired measurements: flow sensor110 and timing mechanism 112 (to measure the urine out flow rate),and/or constituent measuring element(s) 116 (to measure one or moreconstituents).

A component interface 118, which may include one or more physical and/orvirtual interfaces provides connectivity between one or more components110, 112, 116 and a computing unit 120. Component interface 118 may beimplemented, for example, using one or more of: cable interface,wireless channel interface, application programming interface (API),software development kit (SDK) interface, and the like.

Computing unit 120 includes a program store 122 storing codeinstructions for implementation (i.e., instruction execution) byprocessor(s) 124, and/or a data repository 126. Program store 122(and/or data repository 126) may store flow code 122A to calculate theurine output flow rate, constituent code 122B to calculate theconcentration of one or more urinary constituents, and/or other code,for example, instructions to render the GUI that displays the trendand/or the calculated values (as described herein).

Processor(s) 124 may be implemented, for example, as a centralprocessing unit(s) (CPU), a graphics processing unit(s) (GPU), fieldprogrammable gate array(s) (FPGA), digital signal processor(s) (DSP),and application specific integrated circuit(s) (ASIC). Processor(s) 124may include one or more processors (homogenous or heterogeneous), whichmay be arranged for parallel processing, as clusters and/or as one ormore multi core processing units.

Program store 122 stores code instructions implementable by processor(s)124, for example, a random access memory (RAM), read-only memory (ROM),and/or a storage device, for example, non-volatile memory, magneticmedia, semiconductor memory devices, hard drive, removable storage, andoptical media (e.g., DVD, CD-ROM).

Data repository 126 may be implemented as, for example, a memory, alocal hard-drive, a removable storage unit, an optical disk, a storagedevice, and/or as a remote server and/or computing cloud (e.g., accessedusing a network connection).

Computing unit 120 may be in communication (e.g., using a suitableinterface) with one or more user interfaces 128, optionally including adisplay, for example, a touch screen, a mouse, a keyboard, and/or amicrophone with voice recognition software.

Computing unit 120 may include a network interface 130 (e.g., networkinterface card, wireless network connection, cable connection, virtualnetwork interfaces, and the like) for connecting with one or moreservers 132 over a network 134, for example, for transmitting themeasurements to a remote monitoring server (e.g., located at a nurse'sstation) over a local wireless network, for transmitting themeasurements to a storage server at a family physician's office over theinternet.

Computing unit 120 may be implemented, for example, as a stand-aloneportable unit (designed to be transferred between patient beds), ahardware card (or chip) implemented within an existing computer (e.g.,desktop computer located on the ward), and/or a computer program productloaded within the existing computer (e.g., physician's laptop), and/oras an application on a mobile device (e.g., Smartphone, tablet, wearablecomputer such as computer glasses).

Reference is now made to FIG. 3, which is a schematic of an environmentin which system 100 is implemented, in accordance with some embodimentsof the present invention. Urine outputted by a patient 311 is receivedby a urine analyzer 312. The patient may be a hospitalized patient, apatient in a nursing home, or a patient being treated at home. The urineoutputted by the patient may be collected by a catheter, optionally anindwelling urinary catheter (e.g., Foley catheter) that drains out theurine from the bladder as the urine is produced by the kidneys.

The urine is received and analyzed (as described herein) by urineanalyzer 312, which may include one or more of the following componentsdescribed with reference to FIG. 1: inlet 102, dripper element 104, dripchamber 106, outlet 108, flow sensor 110, timing mechanism 112, andconstituent measuring element(s) 116. Urine analyzer 312 may beimplemented as standalone portable device that may be positioned by thepatient's bed. Urine analyzer 312 may be entirely disposable, or includeone or more disposable components.

Signals generated by flow sensor 110, timing mechanism 112, and/orconstituent measuring element(s) 116 are received and processed by a hub313. Hub 313 may be an external unit in electrical communication withurine analyzer 312 (e.g., by a cable and/or wireless channel, and/ornetwork), and/or hub 313 and urine analyzer 312 may be integrated into asingle unit. Hub 313 may correspond to computing unit 120 described withreference to FIG. 1.

A main console 314 may be implemented as a display, optionally atouchscreen, and/or including a user input interface (e.g., buttons,keys), to display the calculated urine output flow rate and/orconstituent concentration (i.e., urine data). Main console 314 maycorrespond to user interface 128 described with reference to FIG. 1.

Referring now back to FIG. 2, at 202, urine outputted by the patient isreceived by system 100.

System 100 operates under the assumption that urine received by inlet102 is an accurate reflection of real-time urine production by thekidneys, within a tolerance requirement (e.g., range) representingremaining urine and/or variation in urine output due to urine within thebladder, leaks, and urine remaining within the catheter.

Inlet 102 may be implemented as a plastic tube, optionally flexible,optionally disposable that is sized to fit to the catheter. Inlet 102may be integrated with the catheter.

At 204, the received urine is formed into drops by drop formationelement 104, for example, a thin hollow tube sized and shaped to formindividual drops at the opposite end of the end receiving the urine.Drop formation element 104 is sized and/or shaped and/or otherwisedesigned to not act as a bottleneck in the flow of urine. The rate atwhich drop formation element 104 is able to form the drops is designedto match the rate of urine outputted by the patient, such that dropformation element 104 does not act as a bottleneck in the flow of urineand inaccurately affect the estimation of the urinary flow rate.

The formed drops drip down into drip chamber 106, one drop at a time.The rate of the formation and dripping of the drops may be related tothe urine output flow rate. Urine drops formed by the kidneys of thepatient flow through the catheter for real-time analysis. Urine formedby the patient may not necessarily accumulate, other than, for example,the urine stored within the catheter and some residual urine within thebladder.

At 206, each drop is sensed, optionally imaged by flow sensor 110 and/ortimed by timing mechanism 112. Inventors discovered that the volume ofthe drops of urine varies according to the make-up of the urine, forexample, as shown by measured drop volume data for different liquids inFIG. 20 of International Patent Application No. WO2016084080. Since thevolume of each drop varies according to the urine of the patient, whichcan vary dynamically for the same patient, the volume of a drop of urinecannot be accurately estimated. Measuring the volume of each drop ofurine provide an accurate calculation of the urine output flow rate.

The volume of each drop is estimated by flow sensor(s) 110. Timingmechanism 112 measures the time of each drop (e.g., the elapsed timebetween drops, and/or the absolute time of each drop according to theactual time). The urine output flow rate is calculated according to thetime and the volume measurements.

Flow sensor(s) 110 analyzes the drops of urine within drip chamber 106,prior to the flowing urine entering a urine collection bag in fluidcommunication with the outlet, for example, in comparison to othermethods that determine the volume of fluid from the urine collectedwithin the urine collection bag.

Reference is now made to FIG. 4, which is a schematic of an exemplaryurine analyzer 401 that outputs signals used to estimate the volume of adrop of urine and/or estimate the urine output flow rate (i.e., signalsof the time of the drop), in accordance with some embodiments of thepresent invention.

Urine outputted by the patient is received by an inlet 412, which maycorrespond to inlet 102 described with reference to FIG. 1, and/or mayconnect to inlet 102, and/or may be an output of dripper element 104.Inlet 412 releases individual drops 414 of urine into a transparent (ortranslucent) inspection capsule 411 (which may correspond to dripchamber 106 described with reference to FIG. 1, and/or may be locatedwithin and/or in communication within drip chamber 106).

Each drop falling from inlet 412 triggers a detector 416, which may beimplemented for example, as a photo sensor. Detector 416 may senseelectromagnetic radiation (e.g., visible light, infrared light, laser)emitted by a source 415, for example, a laser, a light bulb, and/or alight emitting diode (LED). Source 415 and detector 416 may bepositioned opposite each other, such that light from source 415 passesacross the lumen of capsule 411 to reach detector 416. Falling drop 414affects (e.g., disrupts, interrupts, and/or scatters) theelectromagnetic transmission from source 415 to detector 416, generatinga trigger signal 417.

Optionally, trigger signal 417 is used to determine the time of thetriggering drop (e.g., relative elapsed time between drops, and/orabsolute time of the drop) by timing mechanism 112 (e.g., circuitry,code instructions executed by one or more processors). Timing mechanismmay be implemented including source 415 and detector 416.

A fast gated camera 418 is activated by trigger signal 417 outputted byphoto detector 416 located above camera 418. Fast gated camera 418 may ahigh resolution image sensor, for example, a complementary metal oxidesemiconductor (CMOS) module, and/or a charge couple device (CCD) module.

Camera 418 captures one or more images of each drop. An illuminationelement 419 (e.g., light) illuminates drop 414. The illumination mayimprove the quality of the image, by improving the accuracy of theestimation of the volume of the drop. Code instructions (e.g., flow code122A) estimate the volume of each drop according to an analysis of theimage of the drop, as described herein. Illumination element 419 may bepositioned on the same side of capsule 411 as camera 418, or on theopposite side of camera 418. Illumination element 419 may be integratedwith camera 418.

Optionally, the volume of the drop and/or the concentration of theurinary constitutes in the drop is calculated by calculating a type ofcontent of the drop by combining multiple time sequentially orderedcalculated values of widths of the drop, and time sequentially orderedvalues of widths of exemplary drops. The exemplary drops (e.g., storedin a template or library in data repository 126, based on empiricallycollected data and/or data calculated using a mathematical model)include different content types of liquid. The respective drop iscalculated to be a one of the types of liquid, which allows forestimation of the volume and/or estimation of the concentration (e.g.,osmolarity and/or osmolality). Additional details are provided, forexample, with reference to WO2016084080.

Alternatively or additionally, the volume of the drop is estimated byconstructing a 3D volume from the 2D images of the drop (e.g., using twocameras positioned at an angle relative to each other, optionallyorthogonally positioned), and calculating the volume of the constructeddrop. For example, the 2D image of the drop may be assumed to besymmetrical and rotated around a central longitudinal axis in theup-down direction to create the 3D volume of the drop.

Alternatively or additionally, as described with detail with referenceto WO2016084080, the volume of the drop is calculated by summing volumesof horizontal planar segments of the drop. The volume of each horizontalplanar segment of a drop is calculated by measuring the electromagneticradiation (EMR) captured in a restricted horizontal planar area during asequence of time intervals. As the drop falls, in each time interval adifferent horizontal segment of the drop interferes with a portion ofEMR in the restricted horizontal planar area. The width of thehorizontal segment of the drop is proportional to the amount of EMR thatis interfered. The volume of the horizontal segment may be calculatedwhen the width of the segment and the velocity of the segment are known.

After being analyzed, drops falling to the bottom of urine analyzer 401may exit at outlet 413 (which may correspond to outlet 108 describedwith reference to FIG. 1, and/or may connect to outlet 108).

Reference is now made to FIG. 5, which is a schematic of an exemplaryurine analyzer that analyzes volume of urine drops and outputs signalsfor calculation of the urine output flow rate, and/or computes andoutputs the urine output flow rate, in accordance with some embodimentsof the present invention.

An inlet urine tube 502 receives urine outputted by the patient. Afalling drop 520 triggers sensor 504 and is imaged by optical sensor(e.g., camera) 510, as described herein. A microcontroller 506 (e.g.,implemented as circuitry and/or code instructions executed by one ormore processors) process the captured images and/or timing signals, andoutputs signals 508 to a hub and/or other computing unit for furtherprocessing and/or presentation on display. Microcontroller 506 mayprocess and output the raw image and/or timing signals from processingby the other computing unit and/or hub. Alternatively or additionally,microcontroller 506 analyzes the images and/or timing signals andoutputs the estimated drop volume and/or calculated urine output flowrate.

The drops (after being images) may be collected in a urine collectionbag 516. Bag 516 (which is optionally disposable) may be replaced byshutting transfer valve 514.

Calibrated chamber 512 may be used to measure the total volume ofaccumulated urine over a significant period of time.

Reference is now made to FIG. 6A, which is a schematic of an exemplarydrip chamber (e.g., 106 described with reference to FIG. 1), and/orinspection capsule (e.g., 411 described with reference to FIG. 4), inaccordance with some embodiments of the present invention. An inlet port602 receives a drop of urine. The drop of urine falls betweentransparent walls 606. The drops of urine accumulate within a pool space608 at the bottom of the drip chamber (and/or inspection capsule), andleave from an outlet port 604. The drip chamber is sized and shaped toaccommodate a drop falling, optionally without contacting walls 606, andhaving a length long enough so that flow sensor 110 and/or timingmechanism 112 are able to time the drop and/or sense the drop.

Reference is now made to FIG. 6B, which is a schematic of the dripchamber and/or inspection chamber of FIG. 6A positioned to accommodatemeasurements performed by flow sensor 110 and/or timing mechanism 112 onthe falling drops, in accordance with some embodiments of the presentinvention.

The walls (i.e., 606) may include indentations (e.g., when the walls aresufficiently thick) to house flow sensor 110 and/or timing mechanism112, and/or may include apertures 609 that transmit electromagneticradiation (e.g., windows, when the walls are not fully transparent or atrisk of becoming dirty), and/or may be sufficiently transparent suchthat indentations and/or apertures 609 are not required. One or more ofthe following components (described in detail herein) are housed inindentations of the wall and/or positioned next to apertures 609:illumination source 610 (e.g., laser, LED), detector 612 (trigged bysource 610), camera having conventional focusing lens or a telecentriclens 614, and illumination source for camera 616 (e.g., LED). Anoptional constituency analyzer 620 (that analyzes urine constituency asdescribed herein) may be positioned below camera 614 and/or illuminationsource 616 to analyze the urinary constituents of the drops.Microcontroller 618 and/or interface 622 (e.g., to an external computingunit and/or hub and/or display) may be integrated within (and/orpositioned externally to) the walls of the drip chamber and/orinspection chamber.

At 208, the volume of the drop is estimated. The volume is estimatedusing the signal outputted by flow sensor 110 (e.g., image(s)). Theurine output flow rate is calculated according to the volume of the dropand the timing signals outputted by timing mechanism 112. The volumeestimation and/or the urine output flow rate may be calculated by flowcode 112A executed by processor(s) 124 of computing unit 120.

Optionally, the instantaneous urine output flow rate is measured. It isnoted that the instantaneous flow rate is an approximation of theinstantaneous flow rate based on an estimation of the flow rate of theindividual drops. The instantaneous urine output flow rate may bemeasured using one or two drops, based on the relative time between thetwo drops. The flow rate may be measured using a larger number of drops,based on the total measured time for the drops, for example, based on 3drops, 10 drops, or 50 drops, or 100 drop, or a larger number of drops,or the number of drops falling within about 1 second, about 1 minute,about 5 minutes, about 10 minutes, or 30 minutes, or 60 minutes, orother time units. The unit basis for which the urine output flow ratemay be selected according to clinical relevance, accuracy inmeasurement, ability to present the points on a display, and/or otherfactors.

Reference is now made to FIG. 7, which is a schematic of processed dropimages obtained by a sensor, in accordance with some embodiments of thepresent invention. Image 702 is an exemplary image as captured by thegated camera. Image 702 may be processed (e.g., using image processingcode instructions executed by one or more processors) to segment theimage of the drop, shown as image 704. For example, image 702 may beprocessed using a binary filter, to create a binary image 704, whereblack represents the volume of the drop. Optionally, one or more imagesare captured for each drop, for example, 2, 3, 5, or more images. Thebest image may be selected, or multiple images may be analyzed per dropwith the results averaged.

d_(i) denotes a measurement of a horizontal cross section (or slice)obtained from image 704, for example, using image processing methods.

The volume of one or more drops (i.e., accumulated total volume of thedrops) over a unit of time may be calculated using the equation:

V_(drop)=KΣ₁ ^(n)d_(i) ²

where:

V_(drop) denotes the volume of the drop, or accumulated volume of drops(e.g., in milliliters),

K denotes a calibration constant dependent on the camera scalinggeometry,

n denotes the number of drops over the unit of time,

d_(i) is as shown with reference to image 704, and described above.

Alternatively or additionally, the above volume equation may be used toestimate the volume of each drop, using multiple images acquired of eachdrop, and multiple cross sections areas calculated for each drop. Eachimage may be analyzed to calculate the cross sectional area for adifferent part of the drop. Each cross section may be estimated to havea uniform on interpolated thickness estimated between sequential crosssections. Summing the volume of the cross sectional volumes provides thetotal volume of the drop. Additional details may be found, for example,with reference to WO2016084080.

The urine output flow rate may be calculated as the product of the driprate multiplied by the average drop volume, calculated over apre-determined time interval. The drip rate may be determined based oncounting the number of drops, for example, using flow sensor 110, timingmechanism 112, or another sensor that detects and counts drops. Theaverage drop volume may be calculated, for example, based on a sample ofdrops (e.g., random sample, every predefined number of drops, everypredefined time interval, and the like), a set or all drops, or othermethods as described herein. The time interval may be preset, and/ordefined by a user, for example, about 10 minutes, or 30 minutes, or 60minutes, or other time intervals.

The urine output flow rate may be calculated based on adding the volumeof a sequence of individual drops over the predetermined time interval,or another time during which the sequence of drops were added.

The urine output flow rate may be calculated using the equation:

flow rate=N×V_(drop)

Where:

N denotes the number of drops per unit of time used to determine theaccumulated volume of drops (e.g., number of drops per hour, or singledrop per unit of time, or multiple drops per unit of time),

V_(drop) is the total average volume of the drops over the unit of time.

Optionally, a trend is identified based on multiple urine output flowrate points (e.g., calculated as described above). The trend isindicative of a decrease or increase in the urine output flow rate. Forexample, an upwards trend is indicative that the patient is producingmore urine per unit of time. For example, a downward trend is indicativethat the patient is producing less urine per unit of time. The trend isanalyzed based on a predefine tolerance range that indicates a toleratedrange of values for the patient, which is indicative of a safe and/orhealthy and/or adequate urine output of the patient. Optionally, theidentified trend is indicative of acute kidney injury (AKI).

An indication of the detected AKI may be presented on the GUI and/orprovided as an alert (as described herein). The trend indicative of AKImay be identified, for example, based on the AKI definition as describedwith reference to: Section 2: AKI Definition, Kidney InternationalSupplements (2012) 2, 19-36, Ralib, Azrina Md, et al. “The urine outputdefinition of acute kidney injury is too liberal.” Critical care 17.3(2013): 1, and Labib, Mary, et al. “Volume management in the criticallyill patient with acute kidney injury.” Critical care research andpractice 2013 (2013), all of which are incorporated herein by referencein their entirety.

For example, urine output below the range may be indicative of, forexample, acute renal failure (ARF). For example, urine output above therange may be indicative of, for example, post obstructive dieresis(POD). Optionally, the trend is predictive of a future urine flow ratevalue that falls outside of the predefined tolerance range. For example,in about 6 hours the patient is predicted to have a decreased urineoutput below the lower limit, which may be suggestive of, for example,that the patient is developing ARF. In another example, in about 4 hoursthe patient is predicted to have an increased urine output above theupper limit, which may be suggest of, for example, that the patient isdeveloping POD.

Optionally, an alert is generated when the urine output flow rate isactually outside the tolerance range, or is predicted to fall outsidethe tolerance range in the near future (i.e., the next few hours). Thealert may be transmitted as an instant message to a Smartphone of ahealthcare provider (e.g., nurse, on call physician), presented on theGUI presenting the trend, transmitted and presented on another computingdevice performing monitoring of the patient, or other implementations.

Optionally, the trend is identified according to a least squareregression analysis conducted using a sliding window of a predefinednumber of urine output flow rate measurements. For example, y(0), y(1),y(i), . . . y(n), y(n+1) denote the calculated urine output flow rates,optionally calculated at predefined time intervals, for example, every30 minutes, or every hour, or other units of time. z(i)=ax(i)+b denotesthe identified trend line for the calculated urine outflow rates fromy(0) to y(n) (i.e., the trend is calculated for a sliding window of sizen, optionally for the last n samples, where Δ denotes the time intervalbetween consecutive samples).

The following equations are solved:

${J\left( {a,b} \right)} = {\sum\limits_{1}^{n}\left\lbrack {{y(i)} - {z(i)}} \right\rbrack^{2}}$$\frac{\partial J}{\partial a} = {{0\mspace{14mu} \frac{\partial J}{\partial b}} = 0}$$a = \frac{\sum\limits_{1}^{n}{{y(i)}\left\lbrack {i - {{0.5}\left( {n + 1} \right)}} \right\rbrack}}{\left\lbrack {\sum\limits_{1}^{n}i^{2}} \right\rbrack - {n\left( {n + 1} \right)}}$

At 210, one or more constituent signals are generated based on ananalysis conducted on the urine flowing within the drip chamber. Theconstituent signals are indicative of one or more constituents withinthe urine. The constituent signals are generated for each constituentbeing analyzed.

Exemplary constituents being detected include one or more of: organiccompounds, inorganic compounds, cells (red blood cells, white bloodcells), parts of cells (i.e., from burst cells, for example,hemoglobin), proteins (optionally per type of protein, for example,protein size), urea, chloride, sodium, potassium, ions, creatinine, andglucose.

The concentration may be detected for each constituent. Alternatively,the presence of an amount of constituent (e.g., greater than zero, orgreater than a threshold) is detected, for example, the presence ofblood in the urine, the presence of ketones in the urine, and thepresence of glucose in the urine.

Alternatively or additionally, the constituents are detects as a group,without necessarily considering the composition, for example, the urineosmolality may be estimated. As used herein, the term constituent mayinclude the measurement of urine osmolality or other measurement basedon multiple components.

The drop of urine or a sequence of multiple drops is analyzed prior tourine drop entering a urine collection bag in fluid communication withthe outlet, optionally while the urine drop is within the drip chamber.

The drop of urine is analyzed to identify the constituents after beinganalyzed for calculation of the volume of the drop (i.e., inimplementations that measure both the urine flow rate and theconstituents).

Reference is now made to FIG. 8, which is a schematic of the exemplaryurine analyzer device described with reference to FIG. 5, including aconstituent measurement device 802 that measures the constituents in theurine, in accordance with some embodiments of the present invention.Constituent measurement device 802 may correspond to constituentmeasuring elements(s) 116 described with reference to FIG. 1.Constituent measurement device 802 is positioned below trigger sensor504 and imaging sensor 510 (i.e., below flow sensor 110), to analyzedrops 520 sensed for calculation of the volume of the drop. It is notedthat constituent measurement device 802 is located below trigger sensor504 and imaging sensor 510 (i.e., below flow sensor 110) since theconstituent analysis may affect the ability to calculate the volume ofthe urine, for example, by absorbing the urine during the analysisprocess. Signals 804 processed by processor 506 indicative of theconcentration and/or presence of one or more constituents may betransmitted to an external computing unit, a hub, and/or a display, asdescribed herein.

The falling urine drops fall on respective constituent measuringelements 116 that each sequentially perform measurements of respectiveurine constituents for each respective drops, for example, each drop ofurine is analyze for one respective constituent. Multiple constituentsare analyzed by independently analyzing multiple individual drops. Aconstituent signal indicative of the respective urine constituent of therespective drop is generated and analyzed, as described herein.

Reference is now made to FIG. 9, which is a schematic of animplementation of constituent measuring elements 116 based on a rotatingapparatus 900 that rotates to contact each constituent measuring element116 with a different drop of urine, in accordance with some embodimentsof the present invention.

Urine drops are received from an inlet 902. Falling urine drops triggersensor 904, which may be implemented, for example, as a pair of anelectromagnetic source (e.g., light) and a receiving sensor. It is notedthat sensor 904 may be implemented for example, as sensor 504 of FIG. 5.Sensor 904 may trigger camera 906 for imaging the drop for calculationof the drop volume, triggering rotating turret 908.

Turret 907 includes constituent measuring elements 914 arranged on asurface of a rotating element, which may be positioned at an anglerelative to the falling drop (i.e. to allow the drop to spread along thelength of each element 914), or may be positioned flat (i.e.,horizontally) with drop(s) dripped individually to each constituentmeasuring element 914. The horizontal orientation may avoid potentialinteractions when a single drop passes across multiple elements 914, bypreventing movement of the drops that fell on a certain element 914 fromflowing to another neighboring element 914. Each of constituentmeasuring element 914 estimates a concentration (and/or presence) of adifferent urine constituent in a drop of urine.

Turret 907 turns a predefined amount (i.e., arc length, rotationfraction) to expose a new constituent measuring element 914 to the newfalling drop. The rotation of turret 907 may be triggered by sensor 904,and/or may be triggered based on a predefined time intervalscorresponding to the calculated urine flow rate. Turret 907 may becontrolled by a motor (e.g., servomotor) coupled to sensor 904, and/orcontrolled by a controller.

Each constituent measuring element 914 may be implemented as arespective lab-on-chip (LOC) (e.g., solid state) designed to besensitive to estimate a concentration (or presence) of a differentrespective urine constituent. Each LOC outputs a signal indicative ofthe measured concentration (or presence) of the respective urineconstituent). Each signal is analyzed (e.g., by constituent code 122B)to calculate the concentration of the respective constituent of therespective LOC.

In another exemplary implementation, each constituent measuring element914 includes an impregnated strip media that changes to a differentcolor according to the concentration (or presence) of the respectiveconstituent. Device 900 may include a color camera 908 (e.g., red greenblue (RGB) camera, or multi-spectral imager) sized and/or positioned tosense the changed color of each respective constituent measuring element914. Camera 908 may capture an image of the current constituentmeasuring element 914 at each rotation for a pre-determined amount ofurine drops. Camera 908 outputs a signal indicative of the sensedchanged color. The signal is analyzed (e.g., by constituent code 122B)to calculate the concentration of the respective constituentcorresponding to the sensed changed color.

Rotating turret 907 may be controlled to expose different regions of thesame constituent measuring element 914 to new drops of urine, forexample by tilting the angle of turret 907, and/or backwards-forwardspositioning and/or up-down positioning of turret 907. For example, eachelement 914 may include multiple regions to sense multiple urine drops.After each rotation of turret 907, turret 907 may be repositioned toexpose a new row of regions to the drops. Each turret 907 may be used toanalyze a large number of drops.

Optionally, a rinse element(s) and/or dryer element(s) (e.g., heater,air blower) may be positioned to apply a rinse cycle and/or a dry cycleto constituent measuring elements 914 to provide for re-use with newdrops.

Turret 907 may be disposable, and/or replaceable.

Urine remaining after the analysis falls down, and may exit from anoutlet 912, for example, into a urine collection bag.

Referring now back to block 210 of FIG. 2, alternatively oradditionally, the constituency of the drop of urine is analyzed based onspectral analysis.

Reference is now made to FIG. 10, which is a schematic depictingcomponents of a spectral analysis system 1000 for measuring theconstituent(s) of urine, and a sample spectral output 1002, inaccordance with some embodiments of the present invention. System 1000may simultaneously measure multiple urine constituents within the samedrop 1083. Spectral analysis system 1000 may implemented withinconstituent measurement device 802 (i.e., as constituent measuringelement 116) below flow sensor 110 (or other sensor implementations forcalculating of urine drop volume).

A light source 1081 (e.g., LED, light bulb, multi-colored laser)generates a light 1082 that is directed towards drop of urine 1083 (orportion of the drop). A spectral dispersion element 1084 disperses thelight that passed through drop 1083 to create a spectrum 1085. A multielement detector 1086 senses spectrum 1085 (i.e., the dispersed light).Constituent code 122B instructions when executed by processing unit 120,analyze spectrogram 1085 to identify concentration of one or more urineconstituent within drop of urine 1083.

Graph 1002 is an exemplary spectral intensity graph generated based onoutput of multi element detector 1086. Each lambda_(i) denotes adifferent urine constituent. The spectral intensity may be indicative ofthe relative concentration of the respective constituent.

Alternatively, in another implementation, source 1081 is a tunablesource that is adjustable to emit a selected wavelength (or sub-range)from a range of wavelengths of light. A single detector may beimplemented instead of multi element detector 1086. Source 1081 may besequentially turned to different wavelengths for measurement by thesingle detector. The signals may be sequentially analyzed to identifyeach constituent corresponding to the selected wavelength.

Reference is now made to FIG. 11, which is a schematic of an exemplaryimplementation of a constituent analyzer 1100 based on spectral analysis(as described with reference to FIG. 10), in accordance with someembodiments of the present invention. Constituent analyzer 1100estimates, in real time, the osmolarity and/or osmolality and/or thespectral content (which may be used to identify concentration ofindividual constituents) of one or more drops of the patient.

Light source 1191 may be a sweeping source. Light produced by source1191 is directed by lens 1192 to analyzed sample 1195 (i.e., urine drop)positioned on a prism 1194. Urine drops may be directed to prism 1194(i.e., spectral dispersion element) by a drip directing mechanism, forexample, one or more drops may be directed for analysis at selected timeintervals, for example every 30 minute, or every hour, or based on amanual selection, or other periods of time.

Optionally, prism 1194 is a TIR prism that splits the light to twoportions. A first portion of the light 1193 is totally (or mostly)reflected (i.e., does NOT pass through urine 1195). Light 1193 isdirected to an illuminated portion 1199 of an array detector 1198. It isnoted that certain portions 1199 of array detector 1198 are illuminated,while other dark portions 1190 remain un-illuminated. Portion of light1193 reaching illuminated portion 1199 of detector 1198 is based on raysarriving at a certain critical angle that are reflected by prism 1194.Portion of light 1193 reaching illuminated portion 1199 is association(e.g., a function of) the refractive index of urine 1195. The refractiveindex is a function of multiple constituents in urine 1195, also termedosmolarity. The intensity and/or location(s) of illuminated portion 1199(and/or the location(s) of dark portion 1190) relative to array detector1198 may be analyzed to estimate the osmolarity of the urineconstituents, for example, by constituent code 122B.

A second portion of the light 1196 passes through urine 1195. The passedlight is directed by another lens 1192B to another detector 1197,optionally that includes a single detection element. When source 1191 isswept as a function of time, the output of detector 1197 as a functionof time may be graphed as the optical spectrum of urine 1195, andanalyzed (e.g., by constituent code 122B) to calculate one or moreconstituents of the urine (i.e., according to the wavelength(s)outputted by source 1191).

Reference is now made to FIG. 12, which is a schematic of anotherexemplary implementation of constituent analyzers 1200A-B based onspectral analysis (as described with reference to FIG. 10), inaccordance with some embodiments of the present invention.

Constituent analyzers 1200A-B are based on an interferometer design.Analyzer 1200A is based on a Michelson interferometer design, andanalyzer 1200B is based on a Mach-Zender interferometer design.Analyzers 1200A-B include a tunable source 1201A-B capable of emitting arange of wavelengths, for example, a vertical-external-cavitysurface-emitting-laser (VECSEL).

With reference to analyzer 1200A, a beam splitter (BS) 1203A splits thebeam generated by tunable source 1201A to a first reference path 1205Athat is reflected back to beam splitter 1203A by a mirror 1206 that isoptionally adjustable. Beam splitter 1203A splits the beam generated bytunable source 1201A to a second path that passed through a urine sample1204, and is reflected back to beam splitter 1203A through urine sample1204 by another mirror 1207. Beam splitter 1203A combines the beamsreflected by mirrors 1206 and 1207, and directs the combined beams to adetector 1202 that outputs a signal that may be analyzed to estimate theconcentration of constituents in the urine (e.g., osmolarity and/orosmolality) by constituent code 122B executed by processing unit 120.

With reference to analyzer 1200A, a BS 1203B splits the beam generatedby tunable source 1201B to a first reference path 1205B and a secondpath that passes through urine sample 1204. Path 1205B and path throughurine sample 1204 are combined by another beam splitter 1220 for sensingby a detector 1202B that outputs a signal that may be analyzed toestimate the concentration of constituents in the urine (e.g.,osmolarity and/or osmolality) by constituent code 122B executed byprocessing unit 120.

It is noted that additional mirrors may be used to direct the beams oflight, for example, as shown in FIG. 12.

Urine sample 1204 may be stored within a transparent (or partiallytransparent) chamber positioned within drip chamber 106. The transparentchamber is designed to remain in a state filled with urine, optionallywithout air residing in the transparent chamber. Optionally, each newdrop of urine displaces a corresponding volume from the chamber (e.g.,out through outlet 1208), maintaining the chamber in a filled state. Thechamber is position such that the light along the path through urinesample 1204 passes through walls of the transparent chamber and throughthe urine sample 1204 within the transparent chamber.

It is noted that different implementations described herein may besimultaneously implemented in the same device, for example, analyzer1200A described with reference to FIG. 12 may be installed to measurethe urine osmolarity and/or osmolality, and device 900 described withreference to FIG. 9 may be installed to measure the concentration ofcertain urine constituents.

At 212, signals outputted as described with reference to block 210 areanalyzed by constituent code 122B executed by processor(s) 124 toestimate the concentration of one or more urine constituents (i.e.,concentration per constituent), the presence of one or more urineconstituents (i.e., the presence of each constituent) optionally above athreshold (e.g., zero, a concentration threshold), and/or the osmolarityand/or osmolality of the urine.

As used herein, the term concentration (of urinary constituents)sometimes refers to one or more of the following: the concentration ofone or more urine constituents (i.e., concentration per constituent),the presence of one or more urine constituents (i.e., the presence ofeach constituent) optionally above a threshold (e.g., zero, aconcentration threshold), and/or the osmolarity and/or osmolality of theurine.

Constituent code 122B may analyze spectral intensity graph 1002(described with reference to FIG. 10) generated based on output of multielement detector 1086. Each lambda_(i) denotes a different urineconstituent. The spectral intensity may be indicative of the relativeconcentration of the respective constituent.

Alternatively or additionally, constituent code 122B may analyze thecombined spectral signals outputted by analyzers 1200A-B described withreference to FIG. 12. Reference is now made to FIG. 13, which includessignals and/or graphs used to extract concentrations of one or moreurinary constituents from the signal(s) outputted by analyzers 1200A-B,in accordance with some embodiments of the present invention.

Graph 1302 denotes the signal outputted by detector 1202A-B describedwith reference to FIG. 12. The intensity of the signal (e.g., inmilliamps (mA) or millivolt (mV)) may be plotted as a function ofwavelength, and/or position along a detector array. Graph 1304 denotesan analysis of the signal of graph 1302, to identify constituents with ahigher concentration than a normal level. For example, in the exampleshown, Na, K, and Br have elevated concentration in the urine.

The signal may be analyzed, for example, based on a least squareminimization method to identify with a corresponding point of acalibration curve, a predefined function and/or template representingempirically derived measurements (and/or mathematically calculatedestimates based on a model).

Reference is now made to FIG. 14, which is an example of a calibrationcurve 1402 for estimating concentration of a certain urinaryconstituent, in accordance with some embodiments of the presentinvention. Calibration curve 1402 denotes a calibrated spectrum ofintensity as a function of wavelength for a certain urinary constituent(or a certain combination of constituents). Curve 1402 may be createdbased on empirical measurements, and/or based on a mathematical model.

When the sensor (any relevant implementation described herein) outputsan intensity for a wavelength λ, the concentration of the correspondingurinary constituent (denoted as c_(i)) may be estimated using thecalibration curve (denoted as f_(i)) by minimization of a least squaresfunction mathematically represented as:

$J = {\int{\left\lbrack {{g(\lambda)} - {\sum\limits_{1}^{n}{c_{i}{f_{i}(\lambda)}}}} \right\rbrack^{2}d\; \lambda \mspace{14mu} {from}\mspace{14mu} \lambda_{1}\mspace{14mu} {to}\mspace{14mu} \lambda_{2}}}$$\frac{dj}{d\; c_{i}} = {0\mspace{14mu} {\forall{i\mspace{14mu} 1\mspace{14mu} \ldots \mspace{14mu} n}}}$And  assume  no  correlation  between  the  constituents  spectrai.e.  ∫_(λ 1)^(λ n)f_(i)(λ)f_(i)(λ)d(λ)  for  i ≠ j$c_{i} = \frac{j\; {g(\lambda)}{f_{i}(\lambda)}d\; \lambda}{j\; {f_{i}^{2}(\lambda)}d\; \lambda}$

At 214, the calculated urinary flow rate and/or the estimatedconcentration of urinary constituent(s) is presented on a display (e.g.,user interface 128), optionally within a GUI.

Optionally, as each new measurement is performed in real-time based onurine drops as they are released from the body of the patient, the newmeasurements are dynamically plotted on the GUI. The trend may beupdated based on the new measurement, optionally by sliding thecalculation window to include the new measurement (and exclude theoldest measurement). A trend line may be plotted on the GUI to visuallyindicate the future prediction of the values.

The trend may be calculated for the urine flow rate, for the measuredurine osmolality and/or osmolarity, the presence of one or more certainurinary constituents (e.g., above zero or another concentrationthreshold), and/or the concentration of one or more certain urinaryconstituents.

Reference is now made to FIG. 15, which is a schematic of an exemplaryGUI presented on a display indicating the measured urine output flowrates, in accordance with some embodiments of the present invention.

In the example GUI, the current (i.e., instantaneous) flow rate ismeasured as 0.45 ml/Kg*hour, the average flow rate (e.g., based on anaverage of the measurements and/or accumulated calculated volume) forthe last hour is measured as 0.52 ml/Kg*hour. The calculated trend lineis indicating that the urine output flow rate is decreasing. Noprediction of passing the lower value of the same range (0.3 mg/Kg*hour)is made.

At 216, an alert is generated. The alert may be generated according to aset-of-rules, a function, machine learning method, artificialintelligent, or other prediction method (that may be stored in datarepository 126). For example, the alert may be generated when theinstantaneous urine output flow rate is out of the safe range for thepatient, when the trend is indicating that the urine output flow rate ispredicted to fall out of the safe range in a predefine time (e.g., in1-2 hours), when certain constituents are detected in the urine (e.g.,blood, ketones, glucose), when the osmolality and/or osmolarity of theurine is out of a predefined range (or trending out of the range),and/or when the concentration of one or more urinary constituents areout of a predefined range (or trending out of the range).

The alert may be generated, for example, as a flashing message on theGUI, as a text message transmitted to a smartphone of a healthcareprovider, as a beep and message window opening up on a display at anurse's monitoring station, or other implementations.

Reference is now made to FIG. 16, which is a flowchart 1600 of a methodfor calculating concentration of one or more urinary constituents forgenerating the alert, in accordance with some embodiments of the presentinvention.

Detector 1602 represents a multi element detector (as described herein)that may be used to identify one or more urinary constituents, forexample, using the spectral analysis methods described herein thatdirect light to different regions of the detector. For example, cell 1of detector 1602 is used to measure the concentration (or presence) ofleukocytes (i.e., white blood cells) in the urine, cell i denotes anarbitrary cell to measure a concentration of an arbitrary constituents,and cell N is used to measure concentration (or presence of) glucose inthe urine.

At 1604, an average of multiple readings of different urine drops iscalculate for cell i (e.g., optionally for each cell of detector 1602).

At 1606, the average calculated value is compared to a predefinedreference value (e.g., empirically measured and/or mathematicallycalculated based on a model).

At 1608, the concentration is calculated for each urinary constituentaccording to the comparison of block 1606.

At 1610, the alert is generated according to the concentration in viewof the set-of-rules.

At 1612, the alert and/or concentration value may be saved, and/orpresented on a display within the GUI.

At 1614, blocks 1604-1612 are iterated to monitor the urine drops of thepatient.

Referring now back to FIG. 2, at 218, one or more blocks 202-216 areiterated using new urine drops outputted by the patient.

The descriptions of the various embodiments of the present inventionhave been presented for purposes of illustration, but are not intendedto be exhaustive or limited to the embodiments disclosed. Manymodifications and variations will be apparent to those of ordinary skillin the art without departing from the scope and spirit of the describedembodiments. The terminology used herein was chosen to best explain theprinciples of the embodiments, the practical application or technicalimprovement over technologies found in the marketplace, or to enableothers of ordinary skill in the art to understand the embodimentsdisclosed herein.

It is expected that during the life of a patent maturing from thisapplication many relevant sensors will be developed and the scope of theterm sensor is intended to include all such new technologies a priori.

As used herein the term “about” refers to ±10%.

The terms “comprises”, “comprising”, “includes”, “including”, “having”and their conjugates mean “including but not limited to”. This termencompasses the terms “consisting of” and “consisting essentially of”.

The phrase “consisting essentially of” means that the composition ormethod may include additional ingredients and/or steps, but only if theadditional ingredients and/or steps do not materially alter the basicand novel characteristics of the claimed composition or method.

As used herein, the singular form “a”, “an” and “the” include pluralreferences unless the context clearly dictates otherwise. For example,the term “a compound” or “at least one compound” may include a pluralityof compounds, including mixtures thereof.

The word “exemplary” is used herein to mean “serving as an example,instance or illustration”. Any embodiment described as “exemplary” isnot necessarily to be construed as preferred or advantageous over otherembodiments and/or to exclude the incorporation of features from otherembodiments.

The word “optionally” is used herein to mean “is provided in someembodiments and not provided in other embodiments”. Any particularembodiment of the invention may include a plurality of “optional”features unless such features conflict.

Throughout this application, various embodiments of this invention maybe presented in a range format. It should be understood that thedescription in range format is merely for convenience and brevity andshould not be construed as an inflexible limitation on the scope of theinvention. Accordingly, the description of a range should be consideredto have specifically disclosed all the possible subranges as well asindividual numerical values within that range. For example, descriptionof a range such as from 1 to 6 should be considered to have specificallydisclosed subranges such as from 1 to 3, from 1 to 4, from 1 to 5, from2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numberswithin that range, for example, 1, 2, 3, 4, 5, and 6. This appliesregardless of the breadth of the range.

Whenever a numerical range is indicated herein, it is meant to includeany cited numeral (fractional or integral) within the indicated range.The phrases “ranging/ranges between” a first indicate number and asecond indicate number and “ranging/ranges from” a first indicate number“to” a second indicate number are used herein interchangeably and aremeant to include the first and second indicated numbers and all thefractional and integral numerals therebetween.

It is appreciated that certain features of the invention, which are, forclarity, described in the context of separate embodiments, may also beprovided in combination in a single embodiment. Conversely, variousfeatures of the invention, which are, for brevity, described in thecontext of a single embodiment, may also be provided separately or inany suitable subcombination or as suitable in any other describedembodiment of the invention. Certain features described in the contextof various embodiments are not to be considered essential features ofthose embodiments, unless the embodiment is inoperative without thoseelements.

Although the invention has been described in conjunction with specificembodiments thereof, it is evident that many alternatives, modificationsand variations will be apparent to those skilled in the art.Accordingly, it is intended to embrace all such alternatives,modifications and variations that fall within the spirit and broad scopeof the appended claims.

All publications, patents and patent applications mentioned in thisspecification are herein incorporated in their entirety by referenceinto the specification, to the same extent as if each individualpublication, patent or patent application was specifically andindividually indicated to be incorporated herein by reference. Inaddition, citation or identification of any reference in thisapplication shall not be construed as an admission that such referenceis available as prior art to the present invention. To the extent thatsection headings are used, they should not be construed as necessarilylimiting. In addition, any priority document(s) of this applicationis/are hereby incorporated herein by reference in its/their entirety.

What is claimed is:
 1. A urine analysis device for bed side monitoringof a patient, comprising: a drip chamber having an inlet in fluidcommunication with a urine collecting tube for receiving urine from apatient; a rotating element adapted to turn a plurality of measuringelements within the drip chamber below the inlet to successively bringinto contact the plurality of measuring elements with drops of urinereceived from the patient; wherein each of the plurality of measuringelements performs a measurement of a different urine constituent in theurine.
 2. The urine analysis device of claim 1, wherein each of theplurality of measuring elements outputs a signal indicative of themeasurement.
 3. The urine analysis device of claim 1, wherein therotating element is adapted to turn the plurality of measuring elementssuch that each of the plurality of measuring elements is located apredefined amount of time below the inlet.
 4. The urine analysis deviceof claim 3, further comprising: at least one processing unit configuredto receive the signal and to calculate at least one of a concentrationof the respective urine constituent and a presence of the respectiveurine constituent.
 5. The urine analysis device of claim 2, wherein theplurality of measuring elements comprises at least one lab-on-chipsensor adapted to perform the measurement.
 6. The urine analysis deviceof claim 1, wherein the plurality of measuring elements comprises animpregnated strip media.
 7. The urine analysis device of claim 6,wherein the impregnated strip media changes color according to aconcentration of the respective constituent; further comprising a colorsensor adapted to sense the color of the impregnated strip media andoutputs a signal indicative of the color.
 8. The urine analysis deviceof claim 7, further comprising a processing unit adapted to calculate atleast one of a concentration of the respective urine constituent and apresence of the respective urine constituent based on the color.
 9. Theurine analysis device of claim 2, further comprising an outlet in afluid communication with a urine collection bag.
 10. The urine analysisdevice of claim 1, further comprising a sensor adapted to detect one ormore of the drops and to trigger the rotation of the rotating element.11. The urine analysis device of claim 2, further comprising aprocessing unit adapted to instruct a presentation of an indication ofthe measurement on a graphical user interface (GUI) presented on adisplay.
 12. The urine analysis device of claim 11, wherein theprocessing unit is adapted to identify a trend in the urine output flowrate indicative of acute kidney injury (AKI) and to present anindication of the detected AKI on the GUI.
 13. A method of operating aurine analysis device for bed side monitoring of a patient, comprising:providing a drip chamber having an inlet in fluid communication with aurine collecting tube for receiving urine from a patient; andinstructing a rotating element to turn a plurality of measuring elementswithin the drip chamber below the inlet to successively bring intocontact the plurality of measuring elements with drops of urine receivedfrom the patient; wherein each of the plurality of measuring elementsperforms a measurement of a different urine constituent in the urine.14. The method of claim 13, further comprising receiving a signalindicative of the measurement from the respective of the plurality ofmeasuring elements and calculating at least one of a concentration ofthe respective urine constituent and a presence of the respective urineconstituent according to the signal.
 15. The method of claim 13, furthercomprising receiving a signal indicative of the measurement from therespective of the plurality of measuring elements and instructing apresentation of an indication of the measurement on a graphical userinterface (GUI) presented on a display.
 16. The method of claim 13,wherein the plurality of measuring elements comprises an impregnatedstrip media; further comprising receiving a signal indicative of a colorof the impregnated strip media and calculating at least one of aconcentration of the respective urine constituent and a presence of therespective urine constituent according to the color.